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EP1922091A2 - Dispositifs et composites a resistance elevee - Google Patents

Dispositifs et composites a resistance elevee

Info

Publication number
EP1922091A2
EP1922091A2 EP06765297A EP06765297A EP1922091A2 EP 1922091 A2 EP1922091 A2 EP 1922091A2 EP 06765297 A EP06765297 A EP 06765297A EP 06765297 A EP06765297 A EP 06765297A EP 1922091 A2 EP1922091 A2 EP 1922091A2
Authority
EP
European Patent Office
Prior art keywords
acid
polymer
oriented device
anhydride
oriented
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP06765297A
Other languages
German (de)
English (en)
Inventor
Malcolm Brown
Michael Andrew Hall
John Rose
Alan Bull
David F. Farrar
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Smith and Nephew PLC
Original Assignee
Smith and Nephew PLC
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from GB0516943A external-priority patent/GB0516943D0/en
Priority claimed from GB0523318A external-priority patent/GB0523318D0/en
Application filed by Smith and Nephew PLC filed Critical Smith and Nephew PLC
Publication of EP1922091A2 publication Critical patent/EP1922091A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/502—Plasticizers

Definitions

  • This invention relates to biodegradable polymeric devices and composites, particularly to bioresorbable devices and composites and to artifacts made therefrom and their uses.
  • High strength trauma fixation devices plates, screws, pins etc
  • metal typically titanium and stainless steel
  • metal devices have several well known disadvantages.
  • amorphous or semi-crystalline bioresorbable polymers such as poly (glycolic acid) (PGA) and poly (lactic acid) (PLA) are typically used to produce low load bearing devices- such as suture anchors, screws or tacs.
  • PGA poly (glycolic acid)
  • PLA poly (lactic acid)
  • One of the main criteria for using resorbable materials is that they carry out a mechanical function, degrade within a reasonable timeframe (for example, less than 3 yrs), and are ideally replaced by bone when used in bone sites.
  • these materials are not used in high load bearing applications because they are not strong or stiff enough to resist deformation under high load.
  • Drawn P(L)LA fibres and monoliths are also known.
  • drawn materials such as fibres and rods in which the polymer is oriented in the direction of drawing
  • the directional strength is dramatically increased.
  • Products from these combined approaches include fibre reinforced composites, using drawn fibre and a polymer matrix, and self-reinforced materials, using extruded billets which are die drawn into self reinforced rods.
  • WO 01/46501 discloses preparing a melt blend of polyester and multicarboxyiic acid having improved processability in an extruder and also having improved crystallization and absorption properties, envisaged for use in manufacturing nappies.
  • high strength fibres can be produced by incorporating plasticisers in the polymer blend, such as lauric acid, a fatty acid known from WO 03/004071 , to plasticise and accelerate the degradation of P(L)LA, and drawing the fibres to orient the polymer.
  • plasticisers such as lauric acid, a fatty acid known from WO 03/004071
  • the mechanical properties of drawn fibre were not compromised by the incorporation of plasticiser.
  • incorporating these plasticisers increased the degree of draw of the fibres during conventional hot drawing but decreased the drawing temperature.
  • an oriented implantable, biodegradable device formed from a homogeneous polymer blend comprising a poly lactic acid (PLA) in admixture, in an amount of not more than 10% by weight of the polymer blend, with an additive which plasticises polymer draw and which is a degradation accelerant wherein polymer comprised within the polymer blend is in uniaxial, biaxial or triaxial orientation.
  • PVA poly lactic acid
  • the additive is biocompatible.
  • the additive may be suitable for any application and is advantageously suitable for use in medical applications.
  • the additive is a carboxylic acid or precursor thereof.
  • an acid precursor is a carboxyl containing compound and is selected from an acid anhydride, ester or other acid precursor.
  • the acid may be a mono or poly saturated or unsaturated acid, more particularly a mono or diacid.
  • the acid is a monoacid or precursor thereof.
  • the acid is suitably a C 4- 24 carboxylic acid or precursor.
  • suitable additives include the group consisting of hexanoic acid, octanoic acid, decanoic acid, lauric acid, myristic acid, crotonic acid, 4-pentenoic acid, 2-hexenoic acid, undecylenic acid, petroselenic acid, oleic acid, erucic acid, 2,4-hexadienoic acid, linoleic acid, linolenic acid, benzoic acid, hydrocinnamic acid, 4-isopropylbenzoic acid, ibuprofen, ricinoleic acid, adipic acid, suberic acid, phthalic acid, 2-bromolauric acid, 2,4- hydroxydodecanoic acid, monobutyrin, 2-hexyldecanoic acid, 2- butyloctanoic acid, 2-ethylhexanoic acid, 2-methylvaleric acid, 3- methylvaleric acid, 4-methylvaleric acid, 2-e
  • the oriented PLA polymer of the invention is characterised by improved degradation properties, equivalent mechanical properties and enhanced draw with respect to the original drawn PLA polymer.
  • Reference herein to an oriented device is to a device comprised of oriented polymer as known in the art, also known as aligned polymer, wherein the polymer is in uniaxial, biaxial or triaxial alignment.
  • polymers comprise discrete polymer chains which may be aligned or oriented to render the polymer in uniaxial, biaxial or triaxial alignment. Alignment or orientation is suitably conferred by further processing in suitable manner and as hereinafter defined.
  • the oriented device of the invention is therefore distinct from polymer which has not been further processed to confer orientation, and in which polymer chains are typically in random alignment. Orientation may be determined by techniques as known in the art for example scanning electron microscopy (SEM), transmission electron microscopy (TEM), differential scanning calorimetry (DSC), X-ray, optical microscopy and the like.
  • a advantageous additive for use in the invention is lauric acid or benzoic acid. This may be employed as the acid per se or, if desired, as a precursor, for example as the anhydride.
  • the additive will not only control the rate of degradation but will delay the onset of the degradation process relative to the acid. This delay may be achieved, aptly by the use of precursors which are convertible to the acidic form of the additive. Suitable precursors are acid anhydrides which will, in an in vivo environment, hydrolyse to the corresponding acid.
  • Example anhydrides include lauric anhydride and benzoic anhydride.
  • the polymer blend will contain not more than 5%, and more aptly not more than 2%, by weight of the additive and typically the blend will contain not more than 1% by weight of the additive.
  • Example blends will contain not more than 2%, ideally not more than 1 %, by weight of the blend of lauric acid or a precursor thereof.
  • the amount of the additive chosen will also depend upon the nature of the additive and the rate of degradation desired.
  • the polymeric component of the polymer blends useful for the invention essentially comprise a biodegradable PLA, including homopolymers, (block) copolymers, blends, individual or mixed isomers and the like, which may be bioresorbable, bioerodible or display any other form of degradation, for example instability to water, heat or acid, polymer.
  • the PLA may be suitable for any application and is advantageously suitable for medical applications, for example is suitable for implantation into the human or animal body.
  • An oriented device of the invention may be single phase (amorphous) or biphasic (semi crystalline and amorphous).
  • Suitably blends are of miscible polymers.
  • Suitable biodegradable PLA's are selected from poly(lactic acid), isomers thereof including P(L)LA, P(D)LA, P(D 1 L)LA, blends and copolymers thereof.
  • a co-polymer for use in the blend of the invention may comprise more than one PLA as hereinbefore defined or may comprise other known biodegradable polymeric components copolymerised therewith, such as polyesters, including poly(lactic acid), poly(glycolic acid), copolymers of lactic and glycolic acids, copolymers of lactic and glycolic acid with poly(ethylene glycol), poly(e-caprolactone), poly(3-hydroxybutyrate), poly(p-dioxanone), poly(propylene fumarate), poly(trimethylene carbonate) and the like.
  • polyesters including poly(lactic acid), poly(glycolic acid), copolymers of lactic and glycolic acids, copolymers of lactic and glycolic acid with poly(ethylene glycol), poly(e-caprolactone), poly(3-hydroxybutyrate), poly(p-dioxanone), poly(propylene fumarate), poly(trimethylene carbonate) and the like.
  • the copolymer is a copolymer with another poly(lactic acid) or with poly glycolic acid, for example a copolymer of poly(lactic acids) such as P(L)LA/P(D)LA copolymer, or a copolymer of poly(lactic acid) and glycolic acid (known as PLA/PGA co-polymer).
  • the blend may, in addition to the additive, consist of a blend of PLAs or copolymers as hereinbefore defined with other biodegradable polymeric components, for example, polyesters, for .
  • a blend of polylactic acid or PLA/PGA co-polymer either alone or in admixture with each other.
  • Molecular weight of the polymeric component may be selected according to the particular polymer to be used and the intended use of the device of the invention, and therefore the required strength and modulus.
  • the polymeric component has number average molecular weight (Mn) in oriented form in the range in excess of 30,000 daltons or alternatively in the range 50,000 to 500,000 daltons.
  • Mn number average molecular weight
  • Molecular weight of the oriented device for higher strength applications, for example oriented fibres may be in the range 100,000 to 400,000 daltons.
  • Molecular weight may be determined in known manner, for example by gel permeation chromatography (GPC), viscometry or the like.
  • polymeric component is selected with an intrinsic viscosity (IV), in the range 1 to 10, and more particularly 2 to 5.
  • IV intrinsic viscosity
  • the oriented device may also contain fillers such as osteoconductive materials and the like and/or biological actives such as hydroxyapatite.
  • the oriented device of the invention may be provided in the form of fibres, drawn monoliths such as rods and the like, spun or moulded devices or may be used to produce high strength composites reinforced by component fibres, drawn monoliths, spun or moulded polymer and the like.
  • Fibres may be continuous or chopped.
  • Reference herein to fibres includes fibres, yarns, strands, whiskers, filaments, ribbons, tapes and the like.
  • Drawn devices may be singly or multiply drawn.
  • the oriented device of the invention is characterised by properties of high strength.
  • the device has a tensile strength in excess of about 150 MPa up to about 2000 MPa depending on the polymer components and the form thereof.
  • Tensile strength may be in the range from about 800 to about 2000 MPa, for example about 800 to about 1000 or about 1000 to about 2000 MPa, for fibre form devices, or in the range about 150 to about 800 MPa for drawn monoliths, spun or moulded polymer. This compares with a tensile strength of undrawn PLA fibres of the order of 70 MPa.
  • the polymer matrix is a bioresorbable polymer, and may be selected from any bioresorbable polymer, for example a polyester, such as PLA or the like and its isomers and copolymers and blends thereof as hereinbefore defined.
  • the polymer matrix is selected from PLA, P(L)LA, P(D)LA, P(D 1 L)LA, PGA, polycaprolactone (PCL) and the like and (block) copolymers and blends thereof.
  • a matrix polymer may be formed from a homogeneous polymer blend comprising the polymer(s) in admixture, in an amount of not more than 10% by weight of the polymer blend, with an additive which plasticises polymer and which is a degradation accelerant as hereinbefore defined.
  • a composite of the invention may also contain fillers such as osteoconductive materials and/or biological actives such as hydroxyapatite in the matrix and/or the oriented device.
  • the composite comprises oriented device present in a known manner, for example provided as random or aligned fibres, a fabric in woven or unwoven or braided form or as a scrim, mesh, preform or prepreg.
  • Fabrics may be mats, felts, veils, braided, knitted, punched, non-crimp, polar-, spiral- or uni-weaves, tailored fibre placement fabrics and the like.
  • Composite may comprise continuous or chopped oriented fibres of the invention.
  • the oriented device may be present in any desired amount, for example in an amount of from about 1 wt% to about 70wt% of the composite.
  • a composite of the invention is biodegradable and may comprise any implantable device where temporary residence only is required.
  • implantable devices include suture anchors, soft tissue anchors, interference screws, tissue engineering scaffolds, maxillo-facial plates, fracture fixation plates and rods and the like.
  • the composite of the invention is characterised by properties of high strength.
  • the composite of the invention has tensile strength in excess of 150 MPa up to 800 MPa depending on the constituent polymer components and matrix polymer and the composite form.
  • Tensile strength is, for example, in the range about
  • a process for the preparation of an oriented device as hereinbefore defined comprising preparing a polymer blend comprising a polylactic acid in admixture, in an amount of not more than 10% by weight of the polymer blend, with an additive which plasticises polymer draw and which is a degradation accelerant as hereinbefore defined, and processing to orient polymer whereby polymer is in uniaxial, biaxial or triaxial orientation.
  • Polymer component is commercially available or may be prepared by processes as known in the art.
  • the polymer blends used for the present invention may be produced by known processes such as solution blending wherein the additive is blended directly into a solution of a polymeric component comprising for example, PLA in chloroform, by melt blending in melt phase, or by dry blending the solid polymer and additive materials and then solution blending the solid mixture with solvent such as chloroform. The solution blend is then dried to form a solid blend or is cast onto a surface and dried.
  • the polymer blend is cast, compression moulded or extruded into a form suitable for shaping and orienting, for example moulding or extruding as monolith such as billets or rods, or fibre or film, and oriented by any known process that induces orientation into a polymer, selected from uniaxial, biaxial or triaxial orientation as hereinbefore defined.
  • Casting or compression-moulding may be conducted by rendering the solid blend in melt phase for shaping into a desired form for orienting.
  • Extrusion may be of powder or pellets as a dry blend from a hopper with extrusion via a suitable die to the desired shape.
  • orienting is by aligning melt phase polymer blend and cooling, more particularly by drawing, spinning or moulding melt phase polymer blend to orient polymer chains in the direction of draw or spin, or axis or direction of moulding, and cooling, such as drawing, for example fibre drawing produces increased strength and modulus fibre, or (hydrostatic) die drawing produces an increased strength or modulus rod or the like, spinning for example gel spinning or solution spinning produces increased strength or modulus fibre, moulding for example Shear Controlled Orientation in Injection Moulding (SCORIM) produces increased strength or modulus fibre, rod or shaped polymer, and the like.
  • high strength oriented device may be produced by processing to orient the polymer using any of the following processes: -
  • polyester fibre e.g. P(L)LA fibre
  • hydrostatic die drawing or die drawing to produce a high strength-high modulus fast degrading polyester rod (e.g. P(L)LA rod);
  • solution processing such as gel spinning or solution spinning (to produce fibre at ambient temperature from solution, with subsequent solvent removal;
  • Drawing, spinning and moulding processes are known in the art. Drawing is undertaken, for example, by feeding the moulded film or extrudate at elevated temperature through a die and drawing the polymer, whereby the polymer chains orient in the direction of drawing, and cooling. Drawing may be conducted in two stages or passes.
  • an oriented device of the invention may be used to prepare a polymer composite as hereinbefore defined.
  • Composites according to the invention may be prepared by providing the oriented device in desired form and combining with matrix polymer as hereinbefore defined.
  • Matrix polymer is suitably combined in solid, solution or melt form with the oriented device in accordance with the invention and hardened for example by moulding, compression moulding or drying.
  • Matrix may be combined by blending, impregnation, infusion, injection or the like as known in the art.
  • an additive- containing blend as hereinbefore defined may be utilized to prepare both oriented device and matrix component of a composite material which is then fabricated into a high strength biodegradable composite device as hereinbefore or hereinbelow defined.
  • an oriented device or a composite thereof as hereinbefore defined as an implantable biodegradable device such as a high strength trauma fixation device suitable for implantation into the human or animal body, for example plates, screws, pins, rods, anchors or scaffolds, in particular suture anchors, soft tissue anchors, interference screws, tissue engineering scaffolds, maxillo-facial plates, fracture fixation plates and rods and the like.
  • Figure 1 illustrates the degradation profile of drawn P(L)LA and drawn P(L)LA/nica acid (LA) fibres with time.
  • Figure 2 illustrates the molecular weight (Mn) change of drawn P(L)LA and drawn P(L)LA/LA fibres with time.
  • the viscous solutions were cast by poured them out into release paper trays, in order to produce thick sheets of polymer suitable for subsequent granulation.
  • the sheets were left to dry for 2 days in the fume cupboard before undergoing the subsequent drying procedure:
  • the sheets were then granulated with the Cumberland mechanical grinder (fitted with 3mm sieve), after having been dipped into liquid nitrogen to render them more brittle. All the granules were further dried under vacuum at 100 0 C for 4 hours, and left under vacuum at room temperature for 3 days.
  • the extruder was fitted with a general-purpose 12mm screw with a 25:1 L/D ratio.
  • the extruder was fitted with a 2mm (diameter) die (coated) with a L/D ratio of 6:1.
  • the fibre was produced using a flat temperature profile of 240° C for all zones.
  • a nominal 0.5mm diameter fibre was produced (using maximum screw speed of 50rpm) and hauled off at a rate of 16 meters per minute.
  • the diameter of the fibre was monitored during the run using a Mitutoyo laser micrometer.
  • the extruded fibre was sealed in a foil pouch containing a desiccant sachet and then stored in a freezer at - 20° C prior to further processing.
  • Fibre drawing was carried out using a customised drawing rig.
  • the rig consists of two sets of godets and heated plate (hot shoe).
  • the godets were preset to rotate at different speeds.
  • the fibre was feed from a spindle, through the 1 st set of godets, drawn over the hot shoe and around the 2 nd set of godets.
  • the drawn fibre was finally collected on a Leesona fibre winder.
  • the fibres were drawn under various temperatures and speeds to produced fibres with different properties as shown in Table 1.
  • Fibre was drawn using a batch zone drawing process.
  • a cylindrical brass zone (outer diameter 25mm, inner diameter 5mm, 63mm length) was attached to a moving plate.
  • the temperature was controlled using a temperature probe connected to the zone and temperature controls.
  • a clamp was fixed at a given height above the zone, 1 metre length of fibre was clamped at 1 end, threaded through the zone (using a brass rod), and the load was attached to the free end of the fibre. Fibre was then drawn under various speed, load and zone temperatures.
  • Carrier gas Helium
  • Table 3 shows the amount of lauric acid contained in each P(L)UVLA fibre.
  • the fibres were subjected to in vitro degradation by immersion in standard phosphate buffer solution (PBS), maintained at 37 0 C.
  • PBS phosphate buffer solution

Landscapes

  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Dermatology (AREA)
  • Medicinal Chemistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Composite Materials (AREA)
  • Materials Engineering (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Compositions Of Macromolecular Compounds (AREA)
  • Materials For Medical Uses (AREA)
  • Biological Depolymerization Polymers (AREA)
  • Artificial Filaments (AREA)

Abstract

L'invention concerne un dispositif orienté implantable et biodégradable conçu à partir d'un mélange de polymères homogène comprenant un acide polylactique mélangé, dans une quantité pas supérieure à 10 % en poids du mélange de polymères, un additif plastifiant l'étirage des polymères et étant un accélérateur de dégradation. Le polymère compris dans le mélange peut être orienté de manière uniaxiale, biaxiale ou triaxiale. L'invention concerne également un composite de celui-ci, des procédés de préparation de celui-ci et le dispositif biodégradable implantable peut être utilisé comme un dispositif de réparation de trauma à résistance élevée conçu pour être implanté dans le corps humain ou d'un animal. Par exemple, le dispositif de réparation de trauma à résistance élevée peut se présenter sous la forme de plaques, de vis, des broches, de tiges, d'éléments d'ancrage ou d'échafaudages.
EP06765297A 2005-08-18 2006-08-16 Dispositifs et composites a resistance elevee Withdrawn EP1922091A2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
GB0516943A GB0516943D0 (en) 2005-08-18 2005-08-18 High strength fibres and composites
GB0523318A GB0523318D0 (en) 2005-11-16 2005-11-16 High strength fibres and composites
PCT/GB2006/003049 WO2007020432A2 (fr) 2005-08-18 2006-08-16 Dispositifs et composites a resistance elevee

Publications (1)

Publication Number Publication Date
EP1922091A2 true EP1922091A2 (fr) 2008-05-21

Family

ID=37671232

Family Applications (1)

Application Number Title Priority Date Filing Date
EP06765297A Withdrawn EP1922091A2 (fr) 2005-08-18 2006-08-16 Dispositifs et composites a resistance elevee

Country Status (6)

Country Link
US (1) US20080305144A1 (fr)
EP (1) EP1922091A2 (fr)
JP (1) JP2009504929A (fr)
AU (1) AU2006281248A1 (fr)
CA (1) CA2619571A1 (fr)
WO (1) WO2007020432A2 (fr)

Families Citing this family (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB0116341D0 (en) 2001-07-04 2001-08-29 Smith & Nephew Biodegradable polymer systems
GB0329654D0 (en) 2003-12-23 2004-01-28 Smith & Nephew Tunable segmented polyacetal
JP2007313009A (ja) * 2006-05-25 2007-12-06 Terumo Corp ステント
AU2007325001B2 (en) 2006-11-30 2014-04-10 Smith & Nephew, Inc. Fiber reinforced composite material
JP5416090B2 (ja) 2007-04-18 2014-02-12 スミス アンド ネフュー ピーエルシー 形状記憶ポリマーの膨張成形
WO2008131197A1 (fr) 2007-04-19 2008-10-30 Smith & Nephew, Inc. Polymères à mémoire de forme multimodaux
ATE505220T1 (de) 2007-04-19 2011-04-15 Smith & Nephew Inc Graft-fixierung
GB0715376D0 (en) * 2007-08-07 2007-09-19 Smith & Nephew Coating
US8129477B1 (en) * 2008-08-06 2012-03-06 Medtronic, Inc. Medical devices and methods including blends of biodegradable polymers
JP5286505B2 (ja) * 2011-01-19 2013-09-11 東洋製罐株式会社 生分解性樹脂組成物
PL2758183T3 (pl) 2011-09-18 2022-10-10 Bio Plasmar Ltd Biodegradowalne doniczki lub naczynia na żywność
US8834915B2 (en) 2012-03-30 2014-09-16 Manli International Ltd. Drug-containing bioabsorbable fibers and implants
US11325281B2 (en) * 2018-07-23 2022-05-10 Ut-Battelle, Llc Rapid manufacturing of tailored preforms
WO2020131172A1 (fr) * 2018-12-21 2020-06-25 Tepha, Inc. Poches résorbables non tissées pour implants de dispositifs médicaux
CN111671981A (zh) * 2020-06-24 2020-09-18 杭州锐健马斯汀医疗器材有限公司 一种界面螺钉鞘用可吸收复合材料及其制备方法

Family Cites Families (102)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3797499A (en) * 1970-05-13 1974-03-19 Ethicon Inc Polylactide fabric graphs for surgical implantation
BE758156R (fr) * 1970-05-13 1971-04-28 Ethicon Inc Element de suture absorbable et sa
US3736646A (en) * 1971-10-18 1973-06-05 American Cyanamid Co Method of attaching surgical needles to multifilament polyglycolic acid absorbable sutures
US4137921A (en) * 1977-06-24 1979-02-06 Ethicon, Inc. Addition copolymers of lactide and glycolide and method of preparation
US4181983A (en) * 1977-08-29 1980-01-08 Kulkarni R K Assimilable hydrophilic prosthesis
US5110852A (en) * 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US4627952A (en) * 1982-09-03 1986-12-09 Celanese Corporation Injection molding process
US4523591A (en) * 1982-10-22 1985-06-18 Kaplan Donald S Polymers for injection molding of absorbable surgical devices
US4438253A (en) * 1982-11-12 1984-03-20 American Cyanamid Company Poly(glycolic acid)/poly(alkylene glycol) block copolymers and method of manufacturing the same
US4636215A (en) * 1984-01-11 1987-01-13 Rei, Inc. Combination tray and condylar prosthesis for mandibular reconstruction and the like
US4990161A (en) * 1984-03-16 1991-02-05 Kampner Stanley L Implant with resorbable stem
US5527337A (en) * 1987-06-25 1996-06-18 Duke University Bioabsorbable stent and method of making the same
JP2561853B2 (ja) * 1988-01-28 1996-12-11 株式会社ジェイ・エム・エス 形状記憶性を有する成形体及びその使用方法
US5444113A (en) * 1988-08-08 1995-08-22 Ecopol, Llc End use applications of biodegradable polymers
US4938763B1 (en) * 1988-10-03 1995-07-04 Atrix Lab Inc Biodegradable in-situ forming implants and method of producing the same
US5633002A (en) * 1988-10-04 1997-05-27 Boehringer Ingelheim Gmbh Implantable, biodegradable system for releasing active substance
FR2641692A1 (fr) * 1989-01-17 1990-07-20 Nippon Zeon Co Bouchon de fermeture d'une breche pour application medicale et dispositif pour bouchon de fermeture l'utilisant
US5108755A (en) * 1989-04-27 1992-04-28 Sri International Biodegradable composites for internal medical use
US5294395A (en) * 1989-09-01 1994-03-15 Ethicon, Inc. Thermal treatment of theraplastic filaments for the preparation of surgical sutures
WO1991003991A1 (fr) * 1989-09-15 1991-04-04 Nauchno-Proizvodstvennoe Obiedinenie Komplexnogo Razvitia Meditsinskoi Tekhniki I Izdely Meditsinskogo Naznachenia 'ekran' Endoprothese de l'articulation de la hanche
US6908466B1 (en) * 1990-06-28 2005-06-21 Bonutti Ip, Llc Surgical devices having a biodegradable material with a therapeutic agent
EP0520177B1 (fr) * 1991-05-24 1995-12-13 Synthes AG, Chur Dispositif résorbable pour renforcer les tendons et les os
US5275601A (en) * 1991-09-03 1994-01-04 Synthes (U.S.A) Self-locking resorbable screws and plates for internal fixation of bone fractures and tendon-to-bone attachment
US5383931A (en) * 1992-01-03 1995-01-24 Synthes (U.S.A.) Resorbable implantable device for the reconstruction of the orbit of the human skull
US5333624A (en) * 1992-02-24 1994-08-02 United States Surgical Corporation Surgical attaching apparatus
AU4381793A (en) * 1992-05-20 1993-12-13 Cytrx Corporation Gel composition for implant prosthesis and method of use
EP0615555B1 (fr) * 1992-10-02 2001-03-21 Cargill, Incorporated Tissu en polymere de lactide, stable a l'etat fondu, et son procede de fabrication
US5437918A (en) * 1992-11-11 1995-08-01 Mitsui Toatsu Chemicals, Inc. Degradable non-woven fabric and preparation process thereof
US5716410A (en) * 1993-04-30 1998-02-10 Scimed Life Systems, Inc. Temporary stent and method of use
CA2127636C (fr) * 1993-07-21 2009-10-20 Cheng-Kung Liu Plastifiants pour fibres utilises pour former des instruments chirurgicaux
US5417712A (en) * 1994-02-17 1995-05-23 Mitek Surgical Products, Inc. Bone anchor
US5626861A (en) * 1994-04-01 1997-05-06 Massachusetts Institute Of Technology Polymeric-hydroxyapatite bone composite
US5634936A (en) * 1995-02-06 1997-06-03 Scimed Life Systems, Inc. Device for closing a septal defect
US5702656A (en) * 1995-06-07 1997-12-30 United States Surgical Corporation Process for making polymeric articles
FI98136C (fi) * 1995-09-27 1997-04-25 Biocon Oy Kudosolosuhteissa hajoava materiaali ja menetelmä sen valmistamiseksi
US5716413A (en) * 1995-10-11 1998-02-10 Osteobiologics, Inc. Moldable, hand-shapable biodegradable implant material
WO1997045147A1 (fr) * 1996-05-28 1997-12-04 1218122 Ontario Inc. Biomateriau resorbable pour implant forme de particules de phosphate de calcium condensees
US5756651A (en) * 1996-07-17 1998-05-26 Chronopol, Inc. Impact modified polylactide
ES2242982T3 (es) * 1996-08-23 2005-11-16 Osteobiologics, Inc. Dispositivo de ensayo manual de materiales.
US5893850A (en) * 1996-11-12 1999-04-13 Cachia; Victor V. Bone fixation device
CA2274004A1 (fr) * 1996-12-03 1998-06-11 Osteobiologics, Inc. Couche polymere biodegradable
US5733330A (en) * 1997-01-13 1998-03-31 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent
SE512050C2 (sv) * 1997-01-21 2000-01-17 Nobel Biocare Ab Rotationssymmetriskt benförankringselement
US5977204A (en) * 1997-04-11 1999-11-02 Osteobiologics, Inc. Biodegradable implant material comprising bioactive ceramic
WO1998053768A1 (fr) * 1997-05-30 1998-12-03 Osteobiologics, Inc. Implant biodegradable, poreux, et renforce par des fibres
GB9717433D0 (en) * 1997-08-19 1997-10-22 Univ Nottingham Biodegradable composites
US6135987A (en) * 1997-12-22 2000-10-24 Kimberly-Clark Worldwide, Inc. Synthetic fiber
US20020022588A1 (en) * 1998-06-23 2002-02-21 James Wilkie Methods and compositions for sealing tissue leaks
GB9814609D0 (en) * 1998-07-07 1998-09-02 Smith & Nephew Polymers
US6248430B1 (en) * 1998-08-11 2001-06-19 Dainippon Ink And Chemicals, Inc. Lactic acid-based polymer laminated product and molded product
SE515572C2 (sv) * 1998-09-09 2001-09-03 Lanka Ltd Implantat, sätt att framställa det och användning av det
US6248108B1 (en) * 1998-09-30 2001-06-19 Bionx Implants Oy Bioabsorbable surgical screw and washer system
US6255408B1 (en) * 1998-11-06 2001-07-03 Poly-Med, Inc. Copolyesters with minimized hydrolytic instability and crystalline absorbable copolymers thereof
AU757391B2 (en) * 1999-02-04 2003-02-20 Synthes Gmbh Bone screw
US6296645B1 (en) * 1999-04-09 2001-10-02 Depuy Orthopaedics, Inc. Intramedullary nail with non-metal spacers
US7033603B2 (en) * 1999-08-06 2006-04-25 Board Of Regents The University Of Texas Drug releasing biodegradable fiber for delivery of therapeutics
US6425923B1 (en) * 2000-03-07 2002-07-30 Zimmer, Inc. Contourable polymer filled implant
US6689350B2 (en) * 2000-07-27 2004-02-10 Rutgers, The State University Of New Jersey Therapeutic polyesters and polyamides
WO2002013701A1 (fr) * 2000-08-17 2002-02-21 Tyco Healthcare Group Lp Sutures et revetements conçus a partir de verre therapeutique resorbable
CA2453050A1 (fr) * 2000-09-06 2002-03-14 A.P. Pharma, Inc. Polymeres degradables de polyacetal
US6605090B1 (en) * 2000-10-25 2003-08-12 Sdgi Holdings, Inc. Non-metallic implant devices and intra-operative methods for assembly and fixation
US6719935B2 (en) * 2001-01-05 2004-04-13 Howmedica Osteonics Corp. Process for forming bioabsorbable implants
GB0116341D0 (en) * 2001-07-04 2001-08-29 Smith & Nephew Biodegradable polymer systems
US6749639B2 (en) * 2001-08-27 2004-06-15 Mayo Foundation For Medical Education And Research Coated prosthetic implant
US6841111B2 (en) * 2001-08-31 2005-01-11 Basf Corporation Method for making a polyurea-polyurethane composite structure substantially free of volatile organic compounds
US6916321B2 (en) * 2001-09-28 2005-07-12 Ethicon, Inc. Self-tapping resorbable two-piece bone screw
US20030125745A1 (en) * 2001-11-05 2003-07-03 Bio One Tech Inc. Bone-fixing device
CN1599598A (zh) * 2001-11-30 2005-03-23 美国辉瑞有限公司 骨生长促进性化合物的控释聚合组合物
WO2003059203A1 (fr) * 2001-12-21 2003-07-24 Smith & Nephew, Inc. Systeme d'articulation articulee
GB0202233D0 (en) * 2002-01-31 2002-03-20 Smith & Nephew Bioresorbable polymers
AU2003225516A1 (en) * 2002-03-26 2003-10-08 Yissum Research Development Company Of The Hebrew University Of Jerusalem Responsive biomedical composites
US7192448B2 (en) * 2002-06-27 2007-03-20 Ferree Bret A Arthroplasty devices with resorbable component
MXPA05002589A (es) * 2002-09-05 2005-09-20 Ambrose Catherine G Microesferas antibioticas para el tratamiento de infecciones y osteomelitis.
JP2006509539A (ja) * 2002-12-12 2006-03-23 オステオテック，インコーポレイテッド 形成可能かつ硬化可能なポリマー骨複合体およびその生成方法
EP1433489A1 (fr) * 2002-12-23 2004-06-30 Degradable Solutions AG Implant osseux poreux biodégradable contenant une membrane de barrière
EP1592728A2 (fr) * 2003-01-16 2005-11-09 Carnegie-Mellon University Polyurethannes biodegradables et utilisation de ceux-ci
US20070043376A1 (en) * 2003-02-21 2007-02-22 Osteobiologics, Inc. Bone and cartilage implant delivery device
US20070065652A1 (en) * 2003-03-13 2007-03-22 Willaim Marsh Rice University Composite injectable and pre-fabricated bone replacement material and method for the production of such bone replacement material
US7012106B2 (en) * 2003-03-28 2006-03-14 Ethicon, Inc. Reinforced implantable medical devices
EP1631206B1 (fr) * 2003-06-12 2007-10-10 Synthes GmbH Clou chirurgical
GB0317192D0 (en) * 2003-07-19 2003-08-27 Smith & Nephew High strength bioresorbable co-polymers
FI120333B (fi) * 2003-08-20 2009-09-30 Bioretec Oy Huokoinen lääketieteellinen väline ja menetelmä sen valmistamiseksi
US7648504B2 (en) * 2003-09-09 2010-01-19 Bioretec Ltd Bioabsorbable band system
JP4251061B2 (ja) * 2003-10-03 2009-04-08 ブリヂストンスポーツ株式会社 ゴルフクラブヘッド
US7699879B2 (en) * 2003-10-21 2010-04-20 Warsaw Orthopedic, Inc. Apparatus and method for providing dynamizable translations to orthopedic implants
EP1711128A4 (fr) * 2004-01-16 2008-07-30 Osteobiologics Inc Implant os-tendon-os
US7378144B2 (en) * 2004-02-17 2008-05-27 Kensey Nash Corporation Oriented polymer implantable device and process for making same
EP1604693A1 (fr) * 2004-06-09 2005-12-14 Scil Technology GmbH Support formé in situ, son procédé de préparation et son utilisation
US20060067971A1 (en) * 2004-09-27 2006-03-30 Story Brooks J Bone void filler
EP1883398A4 (fr) * 2005-02-01 2012-06-06 Osteobiologics Inc Procede et dispositif d'ajout selectif d'agent bioactif a un implant a plusieurs phases
AU2006321915B2 (en) * 2005-12-06 2012-04-26 Covidien Lp Bioabsorbable surgical composition
WO2007066339A1 (fr) * 2005-12-07 2007-06-14 Ramot At Tel Aviv University Ltd. Structures composites pour l’administration de médicaments
AU2006330940A1 (en) * 2005-12-21 2007-07-05 Synthes Gmbh Resorbable anterior cervical plating system with screw retention mechanism
NZ573125A (en) * 2006-06-28 2011-12-22 Gunze Kk Method for preparing biodegradable lactide caprolactone copolymers having a low metal catalyst impurity by subsequent washing with acetic acid and isopropanol
US20080015578A1 (en) * 2006-07-12 2008-01-17 Dave Erickson Orthopedic implants comprising bioabsorbable metal
US8828419B2 (en) * 2006-10-06 2014-09-09 Cordis Corporation Bioabsorbable device having encapsulated additives for accelerating degradation
US8394488B2 (en) * 2006-10-06 2013-03-12 Cordis Corporation Bioabsorbable device having composite structure for accelerating degradation
US8480718B2 (en) * 2006-12-21 2013-07-09 Warsaw Orthopedic, Inc. Curable orthopedic implant devices configured to be hardened after placement in vivo
US7771476B2 (en) * 2006-12-21 2010-08-10 Warsaw Orthopedic Inc. Curable orthopedic implant devices configured to harden after placement in vivo by application of a cure-initiating energy before insertion
JP5600062B2 (ja) * 2007-10-03 2014-10-01 ポリィノボ バイオマテリアルズ ピーティワイ リミテッド 高弾性率ポリウレタン及びポリウレタン／尿素組成物
US8323322B2 (en) * 2007-10-05 2012-12-04 Zimmer Spine, Inc. Medical implant formed from porous metal and method
FI124190B (fi) * 2007-12-05 2014-04-30 Bioretec Oy Lääketieteellinen väline ja sen valmistus

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2007020432A2 *

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CA2619571A1 (fr) 2007-02-22
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